An imaging system comprises a radiation device for providing excitation radiation of at least two different wavelengths, an objective lens for focusing the excitation wavelengths onto a sample to produce fluorescent emission, and a mirror, configured as a geometric beam splitter, disposed in the transmission path of the emission radiation and excitation radiation subsequent to reflection from the sample and collimation by the lens, wherein the mirror is utilized to reflect one of the collimated excitation and emission radiation such that the emission is directed to a detector and the collimated excitation is directed away from the detector.
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14. An imaging system, suitable for use in optically scanning a sample, said imaging system comprising:
a radiation device providing excitation beams comprising radiation of at least wavelengths λ1 and λ2; an objective lens disposed between said radiation device and the sample; means for selecting one of said excitation beams for transmission through said objective lens so as to illuminate the sample, a portion of said one of said excitation beams incident upon the sample being converted into and subsequently emitted as emission radiation, said objective lens further disposed to substantially collimate at least a portion of said emission radiation so as to form a corresponding emission beam transmitted away from the sample; a detector responsive to the wavelength of the emission radiation; and a geometric beam splitter disposed in the transmission path of said emission beam between said radiation device and said objective lens and oriented to provide at least a portion of said excitation beam reflected from the sample in the direction of said means for selecting and at least a portion of said emission beam in the direction of said detector based on the differences in the relative positions of said emission beam and said excitation beam at said geometric beam splitter.
23. An imaging system, suitable for use in optically scanning a sample, said imaging system comprising:
a radiation device providing excitation radiation of at least wavelengths λ1 and λ2; an objective lens disposed between said radiation device and the sample; means for selecting one of said wavelengths for transmission through said objective lens such that said transmitted wavelength is focused and illuminates the sample, whereby the sample subsequently emits emitted and said objective lens substantially collimates at least a portion of said emitted radiation so as to form a corresponding emission beam directed away from the sample, a detector responsive to the wavelength of the emitted radiation; and a geometric beam splitter disposed in the transmission path of said excitation radiation between said radiation device and said objective lens so as to provide at least a portion of said excitation radiation in the direction of said objective lens, said geometric beam splitter further disposed in the transmission path of said emission beam and oriented so as to provide at least a portion of said excitation beam reflected from said sample and subsequently transmitted through said objective lens in the direction of said means for selecting and at least a portion of said emission beam transmitted through said objective lens in the direction of said detector based on the differences in the relative positions of said emission beam and said excitation beam at said geometric beam splitter.
1. An imaging system, suitable for use in optically scanning a sample, said imaging system comprising:
a radiation device providing an excitation beam comprising radiation of at least wavelengths λ1 and λ2; an objective lens disposed between said radiation device and the sample; means for selecting one of said wavelengths for transmission through said objective lens such that said transmitted wavelength illuminates the sample, whereby a portion of said transmitted beam incident upon the sample is converted into and subsequently emitted as emitted radiation, said objective lens further disposed to substantially collimate at least a portion of said emitted radiation so as to form a corresponding emission beam directed away from the sample, a detector responsive to the wavelength of the emitted radiation, and a geometric beam splitter disposed in the transmission path of said excitation beam between said radiation device and said objective lens so as to provide at least a portion of said excitation beam in the direction of the sample, said geometric beam splitter further disposed in the transmission path of said emission beam and oriented so as to provide at least a portion of said excitation beam reflected from said sample and subsequently transmitted through said objective lens in the direction of said means for selecting and at least a portion of said emission beam transmitted through said objective lens in the direction of said detector based on the differences in the relative positions of said emission beam and said excitation beam at said geometric beam splitter.
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This application is a continuation-in-part of commonly-assigned patent application 09/258,484 filed Feb. 26, 1999.
1. Field of the Invention
This invention in general relates to optical scanning systems and, in particular, to scanning systems such as fluorescent microarray readers, DNA micro-array readers, or "bio-chip" readers, in which excitation radiation of various wavelengths are used to produce fluorescence in a scanned sample.
2. Description of the Prior Art
The use of excitation radiation to produce fluorescence in a scanned sample is known. U.S. Pat. No. 5,381,224 issued to Dixon et al. discloses scanning optical imaging systems for macroscopic specimens, the system allowing both confocal and non-confocal imaging to be performed in reflected light. Fluorescent imagers are used to acquire data in experiments that utilize fluorescent labels to identify the state of a sample being tested. In some cases the presence of or lack of fluors in the sample determines the experimental result. In other cases the density of the fluors, a function of the intensity of the radiation emitted from the sample, is the measurement of interest and the experimental result can be inferred by measuring the intensity of the detected radiation.
An example of a process that uses fluorescent labels is the microarray. A microarray is a set of experiments involving DNA (or RNA) bound to a glass substrate. Reference or "target" DNA is spotted onto a glass substrate--typically a one- by three-inch glass microscope slide--where it chemically binds to the surface. Each spot, or sample, of DNA constitutes a separate experiment. "Probe" DNA or RNA which has been labeled with a fluorophor is then introduced to the surface of the slide and is allowed to hybridize with the target DNA. Excess probe DNA that does not bind with target DNA is removed from the surface of the slide in a subsequent washing process.
The experiment allows the binding affinity between the probe and target DNA to be measured to determine the likeness of their molecular structures; complementary molecules have a much greater probability of binding than unrelated molecules. The probe DNA is labeled with fluorescent labels that emit a range of radiation energy centered about and including a wavelength λemission when excited by an external radiation source of a shorter wavelength λexcitation. The brightness of emitted radiation is a function of the fluor density in the illuminated sample. Because the fluor density is a function of the binding affinity or likeness of the probe molecule to the target molecule, the brightness of each sample can be mapped as to the degree of similarity between the probe DNA and the target DNA present. On a typical microarray up to tens of thousands of experiments can be performed simultaneously on the probe DNA, allowing for a detailed characterization of complex molecules.
A scanning fluorescent imager divides the area of interest into a set of discrete image elements referred to as pixels. Each pixel is independently addressed and measured for the presence of fluors. The fluors are excited by an incident excitation beam and a portion of the resulting emitted fluorescence radiation is collected and measured by detection apparatus. Each measurement results in a data point that represents the relative fluor density of the measured pixel. The pixel data is then reconstructed to create a quantified representation of the area scanned.
In a scanning microscope, each pixel is illuminated independently while it is being addressed. The light source is typically a single-wavelength laser device focused down to form a spot of the desired size. Radiation is emitted by the fluors in an outward, hemispherical transmission pattern. A portion of this emitted radiation is collected by beam collection optics and directed to the detection apparatus. Additional radiation collected is radiation from the incident excitation beam which is reflected or scattered by the surface of the sample. The imager optics must discriminate between the two radiation wavelengths by rejecting the excitation radiation and passing the fluorescent radiation. Optical filtering components, such as dichroic and band pass filters, provide the discrimination in conventional systems.
Laser fluorescence micro-array scanners incorporate the ability to deliver multiple laser excitation wavelengths so that fluorescence data can be obtained from the sample at two or more emission wavelengths by detecting two or more fluorescent dyes. Such a unique excitation and emission wavelength pair is typically referred to as a "Channel". Many DNA micro-array samples utilize a two-wavelength scanning method, where the results of one wavelength scan are used as control values and the results of the other wavelength scan represent the desired experimental result, as in Differential Gene Expression. As the market and application mature, and a larger variety of suitable dyes become available, the demand for alternative excitation wavelengths and emission bands will increase.
Most scanning confocal microscopes employ a dichroic or multichroic beam splitter for color separation between the excitation radiation wavelength λexcitation and the emission radiation wavelength λemission. U.S. Pat. No. 5,672,880 issued to Kain, for example, discloses a fluorescence imaging system in which fluorescent light emitted by a sample is collected by an objective and passed through a dichroic filter placed along the optical axis between a laser and the objective to direct the fluorescent light onto a photo-detector. Dichroic beam splitters are fabricated using a vacuum deposition process in which inorganic crystalline materials having varying indices of optical refraction are deposited in layers onto optical substrates to create optical filters with specific band-pass and/or band-reject characteristics.
In practice, an optical scanning system may operate utilizing five or more single-wavelength radiation devices producing ten or more unique, but variable, emission bands. These operating parameters impose a specification requirement that the component multichroic optical element be designed so as to reflect all five wavelengths and pass the emission wavelengths. A first drawback to this approach is that such a beam splitter specification may be quite difficult to achieve in practice. Moreover, future improvements and developments in optical scanning systems may necessitate that the systems operate with even more excitation and emission wavelengths, requiring a multichroic beam splitter having an even more demanding specification requirements.
Another drawback of conventional optical scanning systems is the design complexity incurred by the use of single-wavelength radiation devices. By utilizing one or more multi-wavelength radiation devices, with an appropriate wavelength selection device, a more compact, robust optical scanning system can be achieved.
While the art describes a variety of imaging systems for optical scanning, there remains a need for improvements that offer advantages and capabilities not found in presently available scanners, and it is a primary object of this invention to provide such improvements.
It is another object of the present invention to provide an imaging system which can image a sample utilizing two or more different wavelengths of excitation radiation on a single microarray sample.
It is yet another object of the present invention to provide an imaging system which utilizes excitation devices producing two or more wavelengths of radiation.
It is further an object of the present invention to provide an optical scanning system which can be adapted for use with newly-available fluors without incurring the need to reconfigure the imaging system.
Other objects of the invention will be obvious, in part, and, in part, will become apparent when reading the detailed description to follow.
The present invention discloses an imaging system comprising a radiation device providing excitation radiation of different wavelengths, an objective lens for focusing the excitation radiation onto a sample to produce fluorescent emission, and a mirror, configured as a geometric beam splitter, disposed in the transmission path of the emission radiation and excitation radiation subsequent to reflection from the sample and collimation by the lens, the mirror reflecting one of the collimated excitation and emission radiation such that the emission is directed to a detector and the collimated excitation is directed away from the detector. Other features of the invention will be readily apparent when the following detailed description is read in connection with the drawings.
The structure and operation of the invention, together with other objects and advantages thereof, may best be understood by reading the detailed description to follow in connection with the accompanying drawings, of which:
There is shown in
The shutter assembly 30 comprises a first beam splitter 31 which is highly reflective to radiation of wavelength λ1 and highly transmissive to radiation of wavelength λ2. Radiation of wavelength λ1 reflected from the first beam splitter 31 to follow a first transmission path through a first shutter 41, and radiation of wavelength λ2 is transmitted through the first beam splitter 31 to follow a second transmission path through a second shutter 43. Radiation of wavelength λ1, following the first transmission path, is reflected again at a first mirror 33, which is highly reflective to λ1 radiation. The λ1 radiation reflected from the first mirror 33 passes through the first is shutter 41, here shown as open, passes through a first narrow pass filter 45, reflects from a second mirror 35, and reflects from a second beam splitter 37. The second beam splitter 37 is highly reflective to λ1 radiation and is highly transmissive to λ2 radiation. After reflection from the second beam splitter 37, the λ1 radiation is output from the shutter assembly 30 as excitation radiation 39.
Radiation of wavelength λ2 is transmitted along the second transmission path through the first beam splitter 31 to the second shutter 43, here shown as closed. When the second shutter 43 is open, λ2 radiation passes through a second narrow pass filter 47 and through the second beam splitter 37. When the first shutter 41 is closed, λ2 radiation is output (not shown) from the shutter assembly 30 as the excitation radiation 39.
The excitation radiation 39 is emitted from the shutter assembly 30 and reflected to the surface of the sample 55 by an excitation mirror 51. An objective lens 53 is positioned between the excitation mirror 51 and the surface of sample 55 so as to focus the excitation beam 39 to a desired spot size 63 on the surface of the sample 55. In the preferred embodiment, the effective focal length of the objective lens 53 is approximately 6 millimeters. This provides a spot size of about 5 μm from an excitation radiation beam 0.6 millimeter in diameter.
When projected onto the surface of the sample 55, the excitation radiation 39 produces three types of radiation which emanate from the surface of the sample 55. The first type of radiation, a specular reflection beam 65 having wavelength of λ1, results from the reflection of a portion of the incident excitation radiation 39 along a path normal to the surface of the sample 55 (i.e., back along the incident path of transmission). The second type of radiation, a diffuse reflection 67, also of wavelength λ1, is that portion of the excitation radiation 39 reflected from the surface of the sample 55 in an other than normal direction. The reflection path of the diffuse reflection 67 is not confined to the diameter of the incident path of transmission of the excitation radiation 39 because the diffuse reflection 67 is substantially scattered by the surface.
The third type of radiation, an emission radiation 69, is produced by the illumination of fluors in the sample 55 in response to the incident excitation radiation 39. As is well known in the relevant art, such fluors emit when excited by radiation of the proper wavelength. Thus, when illuminated by radiation of wavelength λ1 the fluors in the sample 55 produce radiation of wavelength λemit1, typically 20 to 40 nm longer than the wavelength λ1 of the excitation radiation 39. By way of comparison, the energy of the excitation radiation 39 at the surface of sample 55 is on the order of 1 mW, and the energy of the emission radiation 69 is on the order of 10-11 watts. As can be appreciated by one skilled in the relative art, the signal-to-noise ratio of the emitted power to the excitation power decreases as the size of the specular reflection beam 65 increases and as the amount of the diffuse reflection 67 emanating from the surface of sample 55 increases.
The specular reflection beam 65 and those portions of the diffuse reflection 67 and the emission radiation 69 incident on the sample side of the objective lens 53 are collimated into a composite emission beam 71 comprising radiation of wavelengths λ1 and λemit1. The numerical aperture (NA) of the objective lens 53 is at least 0.5, and is made as large as practical so as to intercept the greatest portion of the emission radiation 69, thus to improve the accuracy of the detection process, as explained in greater detail below. In a preferred embodiment, the objective lens 53 has a numerical aperture of about 0.75.
The composite emission beam 71 is transmitted to a detector 81. An optional broadband mirror 73 may be used to provide a folded transmission path by reflection of the incident composite emission beam 71. By utilizing the broadband mirror 73, the cross-sectional profile of the imaging system 10 can be advantageously reduced. The detector 81 is preferably a photo-multiplier tube, but an avalanche photodiode or a solid state optical detection device can be used in the alternative. The photo-multiplier tube is preferable because of its high sensitivity and adjustable gain. Moreover, the output of the photo-multiplier tube comprises a current that is proportional to the detected radiation power. This current signal can be filtered and then converted to a digital value using an analog-to-digital converter.
A detector filter 75, substantially transmissive to the emission radiation 69 and substantially non-transmissive to the excitation radiation 39, may be disposed in the transmission path of the composite emission beam 71 between the objective lens 53 and the detector 81. The detector filter 75 may comprise either a band pass filter or a long pass filter. The detector filter 75 serves to attenuate most or all of the diffuse reflection 67 such that a filtered emission beam 71", comprising primarily the emission radiation 69 of wavelength λemit, is transmitted to the detector 81. In an alternative embodiment, a focusing lens 77 and an aperture stop 79 may be positioned in the transmission path of filtered emission beam 71" as shown. When used in the imaging system 10, the focusing lens 77 forms a confocal system with the objective lens 53 and images the filtered emission beam 71" onto the detector 81. As can be appreciated by one skilled in the relevant art, there may be provided additional band pass or long pass filters for each excitation and emission wavelength pair utilized in the imaging system 10.
The disclosed embodiments advantageously utilize geometric beam splitting and thereby demonstrate an advantages over conventional dichroic and multichroic beam splitting methods and apparatuses. Where dichroics comprise a glass element designed to reflect particular wavelengths and to transmit others, a geometric beam splitter as utilized in the imaging system 10 disclosed comprises the excitation mirror 51. The excitation is mirror 51 is designed to reflect the excitation radiation 39 to the surface of the sample 55 and to reflect the specular reflection beam 65 from the surface of the sample 55, and is physically sized to allow the detector 81 to receive the maximum amount of the emission radiation 69. The excitation mirror 51 has a major dimension larger than the width of the excitation beam 39 and is placed about 45°C with respect to the transmission path of the excitation beam 39. When properly aligned, the excitation mirror 51 will intercept and redirect substantially all the specular reflection 65 to the shutter assembly 30 and away from the detector 81, thus improving the system signal-to-noise ratio.
The relationship of the numerical aperture of the objective lens 53 to a geometric emission transmission factor (GETF) can be best explained with reference to FIG. 2. GETF is defined as the ratio of: i) the blockage of the composite emission beam 71 resulting from placement of the mirror 51 (and associated mounting components) in the transmission path, and ii) the overall path diameter of the composite emission beam 71. It can be shown, with the following two examples, that a higher numerical aperture will improve the GETF of a particular imaging system.
In the first example, we specify a spot size 63 of approximately 5 μm on the surface of the sample 55 with the excitation radiation 39 having a beam diameter of 0.6 millimeter. This can be achieved if the objective lens 53 has an effective focal length of about 6 millimeters. For an NA of 0.75, the aperture diameter is about 13.6 millimeters to give an aperture area of about 145.26 mm. If the excitation mirror 51 and any associated mounting (not shown) have a diameter of 3.17 mm and are set at a 45°C angle with respect to the transmission path of the composite emission beam 71, the cross-sectional area of blockage is about 5.57 mm2. With this configuration, the GETF is found to be:
In the second example, the objective lens 53 has an effective focal length of 10 millimeters and an NA of 0.30. The aperture diameter is about 6.2 millimeter to give an aperture area of about 30.19 mm2. To produce a 5 μm excitation spot, the input excitation radiation 39 should comprise a beam of about 1.0 millimeter in diameter. If the excitation mirror 51 has a diameter of 2.0 millimeter, the excitation radiation 39 will be completely intercepted, even allowing for some tolerance in position. If the excitation mirror 51 is set at a 45°C angle with respect to the transmission path, the area of blockage is about 2.22 mm2. With this configuration, the GETF is found to be:
That is, the GETF is reduced by a factor of two in the second configuration, demonstrating that the GETF is a function of both lens NA and effective focal length. The excitation spot size is related to the effective focal length and the emission aperture is related to the NA.
In an alternative embodiment, shown in
In the present invention, the incident excitation radiation 39 is scanned across the surface of the sample 55 by any of three methods. In the first method, the shutter is assembly 30 is moved within the imaging system 10, as indicated by arrow 83. In the second method, the objective lens 53 is translated with respect to the surface of the sample 55, as indicated by arrow 85. In the third method, the sample 55 is laterally translated with respect to the imaging system 10, as indicated by arrow 87.
While the invention has been described with reference to particular embodiments, it will be understood that the present invention is by no means limited to the particular constructions and methods herein disclosed and/or shown in the drawings, but also comprises any modifications or equivalents within the scope of the claims.
Patent | Priority | Assignee | Title |
10475846, | May 30 2017 | CITIBANK, N A | Media security validation |
7329860, | Nov 23 2005 | ILLUMINA, INC | Confocal imaging methods and apparatus |
7499166, | May 20 2004 | Regents of the University of California, The | Wide field imager for quantitative analysis of microarrays |
7589315, | Nov 23 2005 | Illumina, Inc. | Confocal imaging methods and apparatus |
7791013, | Nov 21 2006 | ILLUMINA, INC | Biological microarray line scanning method and system |
7813013, | Nov 21 2006 | ILLUMINA, INC | Hexagonal site line scanning method and system |
7960685, | Nov 23 2005 | Illumina, Inc. | Confocal imaging methods and apparatus |
8023162, | Nov 21 2006 | Illumina, Inc. | Hexagonal site line scanning method and system |
8158926, | Nov 23 2005 | Illumina, Inc. | Confocal imaging methods and apparatus |
8884211, | Nov 23 2005 | Illumina, Inc. | Confocal imaging methods and apparatus |
9672678, | Jun 15 2015 | DATALOGIC USA, INC | Method and system of using image capturing device for counterfeit article detection |
9816929, | Nov 23 2005 | Illumina, Inc. | Confocal imaging methods and apparatus |
Patent | Priority | Assignee | Title |
4122348, | May 21 1976 | Elscint, Ltd. | Method of and apparatus for classifying biological cells |
4407008, | Oct 08 1980 | CARL-ZEISS-STIFTUNG, HEIDENHEIM BRENZ, DBA CARL ZEISS | Method and apparatus for light-induced scanning-microscope display of specimen parameters and of their distribution |
5022757, | Jan 23 1989 | MEDISPECTRA, INC | Heterodyne system and method for sensing a target substance |
5329461, | Jul 23 1992 | Acrogen, Inc. | Digital analyte detection system |
5381224, | Aug 30 1993 | AE DIXON | Scanning laser imaging system |
5399866, | Mar 24 1993 | General Electric Company | Optical system for detection of signal in fluorescent immunoassay |
5631734, | Feb 10 1994 | AFFYMETRIX INC , A CORP OF DE | Method and apparatus for detection of fluorescently labeled materials |
5672880, | Dec 08 1994 | INTEGENX INC | Fluoresecence imaging system |
5719391, | Dec 08 1994 | INTEGENX INC | Fluorescence imaging system employing a macro scanning objective |
6121603, | Dec 01 1997 | NEW DIMENSION RESEARCH & INSTRUMENTS, INC | Optical confocal device having a common light directing means |
DE19842153, | |||
DE3821422, | |||
JP10096862, |
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